Device and method for real-time lesion estimation during ablation

ABSTRACT

Disclosed herein are ablation systems and methods for providing feedback on lesion formation in real-time. The methods and systems assess absorptivity of tissue based on a degree of electric coupling or contact between an ablation electrode and the tissue. The absorptivity can then be used, along with other information, including, power levels and activation times, to provide real-time feedback on the lesions being created. Feedback may be provided, for example, in the form of estimated lesion volumes and other lesion characteristics. The methods and systems can provide estimated treatment times to achieve a desired lesion characteristic for a given degree of contact, as well as depth of a lesion being created. The degree of contact may be measured using different techniques, including the phase angle techniques and a coupling index.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.12/742,485, filed 12 May 2010 (the '485 application), now U.S. Pat. No.8,702,690, which is a national stage filing based upon internationalapplication no. PCT/US2008/083828 (the '828 application), filed 17 Nov.2008, now expired, which claims the benefit of and priority to U.S.provisional application No. 60/988,734, filed 16 Nov. 2007 (the '734application). The '485 application, the '828 application and the '734application are hereby incorporated by reference as though fully setforth herein.

BACKGROUND OF THE INVENTION

a. Field of the Invention

The present invention relates generally to an ablation catheter andmethod for estimating lesion characteristics as the lesion is beingformed.

b. Background

Catheters are used for an ever growing number of medical procedures. Toname just a few examples, catheters are used for diagnostic,therapeutic, and ablation procedures. Typically, the user manuallymanipulates the catheter through the patient's vasculature to theintended site, such as a site within the patient's heart. The cathetertypically carries one or more electrodes or other diagnostic ortherapeutic devices, which may be used for ablation, diagnosis, cardiacmapping, or the like.

It is well known to utilize catheters for ablation treatments. Forexample, catheters may be used to accomplish radiofrequency (RF)ablation by transmission of RF energy to a desired target area throughan electrode assembly to ablate tissue at the target site. RF energy maygenerate significant heat, which if not controlled, can result inexcessive tissue damage, such as steam pop, tissue charring, and thelike. Accordingly, a need exists to control the delivery of RF energyand to prevent undesired tissue damage.

Surgical devices and techniques utilizing electrodes to transfertherapeutic energy to tissue are well known. Electrosurgery allows forthe incision, cauterization, fulguration, and desiccation of tissuethrough the application of high-power, radio frequency (RF) energy totissue through an electrode. Ablation techniques, whereby the targettissue is necrotized through coagulation, are also performed usingsurgical devices with electrodes to transfer RF energy to tissue. Manybenefits may be gained by forming lesions in tissue—for example, controlof cardiac arrhythmia or tachycardia, removal of skin diseases, or thetreatment of varicose veins—if the depth and location of the lesionsbeing formed can be controlled. In particular, it can be desirable toelevate tissue temperature to around 50-55° C. until lesions are formedvia coagulation necrosis, which changes the electrical properties of thetissue. For example, when sufficiently deep lesions are formed atspecific locations in cardiac tissue via coagulation necrosis,undesirable ventricular tachycardia may be lessened or eliminated.“Sufficiently deep” lesions means transmural lesions in some cardiacapplications.

Several difficulties may be encountered, however, when attempting toform adequately-deep lesions at specific locations using some existingsurgical ablation electrodes. For example, when forming lesions with RFenergy, high temperature gradients are often encountered in the vicinityof the electrode. At the edges of some existing electrodes are regionsof very high current density leading to large temperature gradients andhot spots. These “edge effects” may result in the formation ofundesirable coagulum and charring of the surface tissue. For example,undesirable coagulum may begin to form when blood reaches around 80° C.for an appreciable length of time, and undesirable tissue charring anddesiccation may be seen when tissue reaches around 100° C. for anappreciable length of time. There two types of undesirable coagulum:coagulum that adheres to and damages the medical device; and coagulumblood clots or curds that may enter a patient's bloodstream, possiblyresulting in other health problems for the patient. Charring of thesurface tissue may also have deleterious effects on a patient.

As the temperature of the electrode is increased, the contact timerequired to form an adequately-deep lesion decreases, but the likelihoodof charring surface tissue and forming undesirable coagulum increases.As the temperature of the electrode is decreased, the contact timerequired to form an adequately-deep lesion increases, but the likelihoodof charring surface tissue and forming undesirable coagulum decreases.It is, therefore, a balancing act trying to ensure that tissuetemperatures are adequately high for long enough to create deep lesions,while still preventing or minimizing coagulum formation and/or charringof the surface tissue.

Generally, a need exists to control the delivery of ablation energy (forexample, RF energy) and to provide feedback on size and other lesioncharacteristics during the ablation process.

The information included in this background section of thespecification, including any references cited herein and any descriptionor discussion thereof, is included for technical reference purposes onlyand is not to be regarded subject matter by which the scope of theinvention is to be bound.

BRIEF SUMMARY OF THE INVENTION

The present invention is directed to improved ablation catheters andmethods useful in conjunction with such ablation catheters.

The present invention provides for an ablation catheter for use incontrolling the delivery of ablation energy during the ablating process.In one aspect, the invention provides for an ablation system forablating tissue in need of treatment, comprising: an ablation catheterhaving at least one electrode; a power source coupled to at least oneelectrode, said power source being programmable to deliver at least oneprogrammable level of power; a voltage measurement device for measuringa voltage signal being delivered to the tissue; a current measurementdevice for measuring a current signal being delivered to the tissue; aphase measurement device to determine an amount of phase change betweenthe measured voltage signal and the measured current signal; a clock tomeasure a time period during which ablative power is delivered by thepower source; and a lesion analysis processor for estimating lesionformation. Preferably, the lesion analysis processor estimates lesionformation as a function of at least: the measured phase change betweenthe voltage signal and the current signal; information indicating theprogrammable power level at which the power source delivers ablativepower to tissue in need of treatment; and the measured time period forwhich ablative power is delivered by the ablation catheter to tissue inneed of treatment. Optionally, the system includes a controller coupledto the power source and the lesion analysis processor for controllingthe power source based on information provided by the lesion analysisprocessor. Optionally, the ablation system includes a tissue temperaturemeasurement device to measure a temperature of the tissue being ablated,and the controller may be coupled to the tissue temperature measurementdevice such that if the temperature of the tissue being ablated exceedsa maximum desirable temperature, the controller will deactivate theablation source. In an exemplary embodiment, the power source is an RFpower source, in which case the lesion analysis processor can estimatelesion formation as a function based on the measured phase changebetween an RF voltage signal and an RF current signal at the point intime when the RF power source is initially activated. In anotherexemplary embodiment, the ablation system has a lesion analysisprocessor that estimates lesion formation as a function based on themeasured phase change between the voltage signal and the current signalat the point during treatment when the lesion is being estimated.

The ablation system may have a single power source operating with one ormore electrodes, in which case, the power source is preferablyprogrammable to deliver assessment power, at a level that is below anablation power level, to assess the degree of contact between thecatheter and the tissue being treated. The single power source can alsobe programmed or controlled to deliver ablation energy to the tissue inneed of treatment, through the same electrode as assessment is done, orthrough a different electrode.

While the degree of contact or electric coupling can be measured usingthe phase angle that exists between the measured voltage signal andmeasured current signal of the assessment voltage, other measurementscan be used as well. For example, the complex impedance, which is thecomplex sum of resistance and reactance, can be measured and used. Inparticular, the phase angle of the complex impedance is the same phaseangle that would be measured by comparing the voltage signal to thecurrent signal. Either technique could be used.

In another embodiment, an alternative to measuring the phase angle canbe used. For example, a coupling index indicative of a degree of contactbetween an electrode and a tissue can be used. The coupling index can becalculated from the components of complex impedance, such as resistance,reactance, impedance magnitude, and impedance phase angle.

In another embodiment, the ablation system of the present invention mayutilize a first power source coupled to a first electrode to deliverablation energy to the tissue, and a second power source coupled to asecond electrode on the catheter to deliver assessment power which willbe measured by the voltage measurement device and the currentmeasurement device to assess the degree of contact between the secondelectrode and the tissue.

Preferably, the lesion analysis processor utilizes a regression analysisof a plurality of previously collected data points to calculate anabsorptivity factor for the tissue being ablated. Each of the pluralityof previously collected data points comprises information respectivelyfor a plurality of lesions, including at least a degree oftissue-electrode contact, a lesion volume, and an ablation power level.The lesion analysis processor can calculate a lesion volume for a lesionbeing created based on a measured amount of phase change, a programmedlevel of ablation power being used to create the lesion; and a timeperiod measured by the clock indicating the time for which the ablationtreatment has been active. Optionally, the controller can be programmedto continue delivering ablation power if the lesion analysis processordetermines that the calculated lesion volume for the lesion beingcreated is less than a desired lesion volume. The controller can also beprogrammed to continue delivering ablation power if the lesion analysisprocessor determines that the calculated lesion volume for the lesionbeing created is less than a desired lesion volume.

Also disclosed herein is a method of providing feedback on lesionformation, in which the an ablation catheter is placed in contact withtissue to be ablated. The catheter can have a tissue-contacting ablationelectrode coupled to an RF energy source for delivering energy to thetissue. The RF energy source is activated to apply RF power at a firstpower level, so that an RF voltage signal can be delivered to the tissueby the tissue-contacting ablation electrode. The RF current signal beingdelivered to the tissue by the tissue-contacting ablation electrode canbe measured, and a degree of electrode-tissue contact can be assessed bydetermining an amount of phase change between the RF voltage signal andthe RF current signal at a point in time before the temperature of thetissue is increased by an application of ablation energy. A regressionanalysis curve can be created to provide information on absorptivityfactors as a function of phase change between an RF voltage signal andan RF current signal. The regression analysis curve can be used todetermine an absorptivity factor corresponding to the determined amountof phase change between the RF voltage and the RF current. The RF energysource can be activated to apply RF power at a second power level todeliver an amount of RF energy effective for ablating tissue. The timefor which the RF energy source is activated at the second power levelcan be monitored, and feedback can be provided to an operator byproviding information on the lesion volume as a function of thedetermined absorptivity factor, the second power level, and the time forwhich the RF energy source is activated at the second power level.

Preferably, the regression analysis is generated using a collection ofdata points for a plurality of lesions created using a plurality ofdifferent degrees of applied contact. Each of the data points ispreferably generated by: placing the ablation catheter into contact withtissue to be ablated and achieving a respective degree of appliedcontact between the ablation catheter and the tissue, applying RF powerat a power level L1 at the respective degree of applied contact;measuring an RF voltage signal being delivered to the tissue; measuringan RF current signal being delivered to the tissue; determining arespective amount of phase change between the measured RF voltage signaland RF current signal at a point in time before the temperature of thetissue is increased by an application of ablation energy; applying RFpower at a power level L2 for a time period TP1 at the respective degreeof applied contact to create a lesion; measuring the respective lesionvolume of the lesion resulting from the application of RF power at powerlevel L2 for a time period TP1 at the respective degree of appliedcontact; and associating the measured respective lesion volume, themeasured respective amount of phase change, power level L2, and timeperiod TP1 to form a respective data point. The regression analysis canthen be used determine absorptivity as a function of changes in phaseangle between an RF voltage signal and an RF current signal. Preferably,the power level L1 is below a level that would be effective to ablatetissue, and the power level L2 is at a level that would be effective toablate tissue, though it is also possible that the power level L1 isabout the same level as power level L2, and each of L1 and L2 are at alevel that would be effective to ablate tissue.

In exemplary embodiments, feedback can be provided using a display,including without limitation, a computer screen and/or a numeric oranalog display. The display can provide information on a calculatedlesion volume for the lesion being created and/or information on atarget lesion volume. If the calculated lesion volume equals or exceedsthe target lesion volume, the ablation energy source can be deactivated.

In another embodiment, temperature of the tissue being ablated can bemonitored and the ablation energy source can be deactivated if thetissue temperature exceeds a target tissue temperature.

The various embodiments can be utilized with ablation sources thatoperate in a constant power mode, where the amount of power beingdelivered is substantially constant over a period of time, or withablation sources that operate in a temperate control mode, in whichcase, the power may fluctuate over time and will be deactivated when thetissue temperature meets a preset level.

Also disclosed is a method of estimating lesion size. The methodincludes placing an ablation catheter in contact with tissue to beablated, said catheter having a tissue-contacting ablation electrodecoupled to an ablation energy source for delivering ablation energy tothe tissue and a contact-assessing electrode coupled to acontact-assessing energy source for delivering contact-assessing energyto the tissue. The contact-assessing energy source is activated todeliver a contact-assessing energy, and the contact-assessing voltagesignal being delivered to the tissue by the contact-assessing electrodeis measured along with the contact-assessing current signal beingdelivered to the tissue by the contact-assessing electrode. The amountof phase change between the contact-assessing voltage signal and thecontact-assessing current signal is determined, which is indicative ofthe degree of electric coupling or contact. The ablation energy sourceis activated to apply ablation energy to the tissue at a preset powerlevel, and the temperature of the tissue being ablated is monitored sothat if the monitored tissue temperature exceeds a maximum desiredtissue temperature, the ablation energy source can be deactivated. Thesize of the lesion being created can be estimated using at least thefollowing: i) the determined amount of phase change between thecontact-assessing voltage signal and the contact-assessing currentsignal; ii) the preset power level; and iii) the time for which theablation energy source is activated.

The ablation energy source being used can be separate from or the samesource as is used for the contact-assessing energy source. When there isa single source, the single source preferably is programmable to delivernon-ablative power for assessing a degree of contact between thecontact-assessing electrode and the tissue to be ablated, and to deliveran ablative power for ablation.

Exemplary methods disclosed herein may also use regression analysis tohelp provide feedback on lesion formation. For example, a validationstudy may be used to create a plurality of lesions, each of which may bemeasured and studied to create data points for use in a regressionanalysis. Preferably, the plurality of lesions are created using varyingdegrees of contact. For each lesion, the degree of contact can beassessed, the volume of the lesion created can be measured and arecording system can be used to record the measured data and thesettings used to create each of the plurality of lesions. A regressionanalysis can then be run on the collection of data stored in therecording system to estimate absorptivity factors for tissue beingablated. The regression analysis can then be used to estimate lesionsize using at least the following: i) the determined amount of phasechange between the contact-assessing voltage signal and thecontact-assessing current signal; ii) the preset power level; iii) thetime for which the ablation energy source is activated; and iv) aestimated absorptivity factor determined using the regression analysis.

According to another aspect of the present invention, an ablation systemfor ablating tissue in need of treatment generally includes: an ablationcatheter having at least one electrode; a power source coupled to atleast one electrode, the power source being programmable to deliver atleast one programmable level of power; a voltage measurement device formeasuring a voltage signal being delivered to the tissue; a currentmeasurement device for measuring a current signal being delivered to thetissue; a contact assessment device that assesses a degree of electricalcoupling or contact between the ablation catheter and tissue beingtreated by determining an amount of phase change between the measuredvoltage signal and the measured current signal; a clock to measure atime period during which ablative power is delivered by the powersource; a power monitoring device to monitor the amount of ablationpower that is delivered by the ablation catheter; a temperature sensorto measure the temperature of the tissue being treated and to monitorfor changes over time; a lesion analysis processor for estimating lesionformation as a function of at least: i) a output of the contactassessment device that corresponds to an amount of phase change betweenthe measured voltage signal and the measured current signal at a pointin time before the temperature of the tissue increases from applicationof ablation energy; ii) information from the power monitoring deviceindicative of the amount of ablation power that is delivered by theablation catheter as a function of time; iii) information from thetemperature sensor indicative of the changes in temperature of thetissue being treated with ablation energy; and a controller coupled tothe power source and the lesion analysis processor for controlling thepower source based on information provided by the lesion analysisprocessor.

Optionally, the controller may be coupled to the tissue temperaturemeasurement device such that, if the temperature of the tissue beingablated exceeds a maximum desirable temperature, the controller willdeactivate the power source.

The lesion analysis processor may include a look up table or graph of aregression analysis of previously measured lesion volumes for aplurality of lesions. This data may be used by the lesion analysisprocessor to calculate an absorptivity factor for the tissue beingablated, and this absorptivity factor may also be used by the lesionanalysis processor to estimate lesion formation.

It is also contemplated that the controller may be programmed to operatethe power supply at a first power level to allow the system to assesselectrical coupling or contact between the catheter and the tissue and asecond power level to ablate tissue.

Also disclosed herein is a method of ablating tissue including thefollowing steps: electrically coupling an ablation catheter with tissueto be ablated, the catheter having a tissue-contacting ablationelectrode coupled to an RF energy source for delivering power to thetissue; activating the RF energy source to supply RF power at a firstpower level; monitoring an RF voltage signal being delivered to thetissue; monitoring an RF current signal being delivered to the tissue;monitoring an amount of phase change between the RF voltage signal andRF current signal while RF power is being delivered to the tissue;activating the RF energy source to supply RF power at a second powerlevel; monitoring a temperature of the tissue to which RF power is beingapplied; obtaining a regression analysis curve that provides informationon absorptivity factors as a function of at least a) a phase changebetween an RF voltage signal and an RF current signal, where the phasechange is indicative of a degree of electrical coupling or contactbetween a catheter and tissue being ablated; and b) a change in tissuetemperature that results from applied ablation energy; using theregression analysis curve to determine an absorptivity factor for tissuebeing ablated, where the regression analysis curve is used to identifythe absorptivity based on a) a measured amount of phase change betweenthe RF voltage and the RF current and b) a measured amount of change intissue temperature which change reflects the application of ablationenergy to the tissue; and calculating a lesion volume as a function ofthe determined absorptivity factor, the difference between the currenttissue temperature and the initial tissue temperature, and the totalamount of ablation energy delivered to the tissue. The RF energy sourcemay be deactivated if the tissue temperature exceeds a maximum tissuetemperature setting. The RF power source may also be deactivated whenthe calculated lesion volume equals or exceeds a target lesion volume.

The regression analysis curve may be obtained by forming a collection ofdata points for a plurality of lesions created using a plurality ofdifferent degrees of applied electrical coupling or contact. The datapoints may be measured as follows for each respective lesion of theplurality of lesions: electrically coupling the ablation catheter withtissue to be ablated and achieving a respective degree of appliedelectrical coupling or contact between the ablation catheter and thetissue; applying RF energy at a power level L1 at the respective degreeof applied electrical coupling or contact; measuring an RF voltagesignal being delivered to the tissue; measuring an RF current signalbeing delivered to the tissue; determining a respective amount of phasechange between the measured RF voltage signal and RF current signal at apoint in time before the temperature of the tissue is increased by anapplication of ablation energy; applying RF power at a power level L2 atthe respective degree of applied electrical coupling or contact tocreate a lesion; monitoring a temperature of the tissue being ablated;monitoring the time period TP1 for which RF power applied at power levelL2 to form a lesion; determining a respective amount of phase changebetween the measured RF voltage signal and RF current signal after theformation of a lesion; measuring the respective lesion volume of thelesion resulting from the application of RF power at power level L2 fora time period TP1 at the respective degree of applied electricalcoupling or contact; associating the measured respective lesion volume,the measured respective amount of phase change prior to any increase intissue temperature the measured respective amount of phase change afterthe formation of a lesion, power level L2, and time period TP1 to form arespective data point; and applying a regression analysis to thecollection of respective data points to generate a graph or lookup tablefor determining absorptivity as a function of at least i) a degree ofelectrical coupling or contact as indicated by changes in phase anglebetween an RF voltage signal and an RF current signal and ii) a changein tissue temperature that results from application of ablation energy.For example, RF power may be applied at power level L2 until the tissuetemperature reaches about 55° C.

According to yet another aspect of the present invention, a method ofestimating lesion size generally includes the following steps: placingan ablation catheter in contact with tissue to be ablated; activatingthe contact-assessing energy source to deliver a contact-assessingenergy; measuring a contact-assessing voltage signal being delivered tothe tissue by the contact-assessing electrode; measuring acontact-assessing current signal being delivered to the tissue by thecontact-assessing electrode; determining an amount of phase changebetween the contact-assessing voltage signal and the contact-assessingcurrent signal at a point in time before activation of the ablationenergy source; activating the ablation energy source to apply ablationenergy to the tissue at a preset power level; monitoring the amount ofablation energy delivered by the ablation energy source; monitoring atime period for which ablation energy is being delivered by the ablationsource; monitoring a temperature of the tissue being ablated; andestimating a size of the lesion being created using at least thefollowing: i) the determined amount of phase change between thecontact-assessing voltage signal and the contact-assessing currentsignal before activation of the ablation energy source; ii) themonitored amount of ablation power delivered by the ablation energysource; iii) the monitored time period for which the ablation energysource is activated; and iv) the change in temperature of the tissue asmeasured before activation of the ablation energy and the current tissuetemperature. Typically, the catheter will include: a tissue-contactingablation electrode coupled to an ablation energy source for deliveringablation energy to the tissue and a contact-assessing electrode coupledto a contact-assessing energy source for delivering contact-assessingenergy to the tissue. Optionally, the method also includes: determiningthat the estimated size of the lesion being created is at or near adesired size and deactivating the ablation energy source.

It is desirable for the contact-assessing energy source to be an RFenergy source that delivers non-ablative power for assessing a degree ofcontact between the contact-assessing electrode and the tissue to beablated. The ablation energy source may also be an RF energy source. Insome embodiments of the invention, the tissue-contacting ablationelectrode is the contact-assessing electrode, and is coupled to aprogrammable RF energy source, such that a non-ablative power may bedelivered for contact assessment and an ablative power may be deliveredfor tissue ablation.

Further disclosed is an ablation system for ablating tissue in need oftreatment. The system includes: an ablation catheter having at least oneelectrode to deliver ablation energy to tissue in need of treatment; avariable power source coupled to at least one electrode; a voltagemeasurement device for measuring a voltage signal being delivered to thetissue; a current measurement device for measuring a current signalbeing delivered to the tissue; a phase measurement device to determinean amount of phase change between the measured voltage signal and themeasured current signal; a power measurement device to measure, as afunction of time, the power being delivered by the power source; and alesion analysis processor for estimating lesion formation as a functionof at least: a measured phase change between the voltage signal and thecurrent signal and information indicating an amount of power that isdelivered to the tissue. The lesion analysis processor may estimate anamount of treatment time necessary to form a lesion, and may alsoprovide real-time feedback on an estimated depth of a lesion beingcreated using the system.

The foregoing and other aspects, features, details, utilities, andadvantages of the present invention will be apparent from reading thefollowing description and claims, and from reviewing the accompanyingdrawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagrammatic illustration of an exemplary tissue ablationsystem which may be implemented to assess electrode-tissue contactduring a tissue ablation procedure for a patient.

FIG. 1a is a detailed illustration of the patient's heart in FIG. 1,showing the electrode catheter after it has been moved into thepatient's heart.

FIG. 2a illustrates exemplary levels of electrical contact or couplingbetween the electrode catheter and a target tissue.

FIG. 2b illustrates exemplary levels of mechanical contact or couplingbetween the electrode catheter and a target tissue.

FIG. 3 is a high-level functional block diagram showing the exemplarytissue ablation system of FIG. 1 in more detail.

FIG. 4 is a model of the electrode catheter in contact with (or coupledto) target tissue.

FIG. 4a is a simplified electrical circuit model corresponding to themodel shown in FIG. 4.

FIG. 5 is an exemplary high level functional block diagram for a phasedetection circuit that may be implemented in the tissue ablation systemfor assessing electrode-tissue contact or coupling.

DETAILED DESCRIPTION OF THE INVENTION

Exemplary embodiments of a tissue ablation system and methods of use toestimate characteristics of lesions being formed are depicted in thefigures. As described further below, the tissue ablation system of thepresent invention provides a number of advantages, including, forexample, the ability to estimate lesion characteristics during theablation process and thereby reduce the likelihood of complicationsassociated with applying excessive ablative energy to a target tissue.The invention also provides for enhanced lesion estimation andformation.

FIG. 1 is a diagrammatic illustration of an exemplary electrode cathetersystem 10 which may be implemented to estimate lesion characteristicsduring a tissue ablation procedure for a patient 12. Catheter system 10includes an electrode catheter 14, which may be inserted into thepatient 12, e.g., for forming ablative lesions inside the patient'sheart 16. During an exemplary ablation procedure, a user (e.g., thepatient's physician or a technician) may insert the electrode catheter14 into one of the patient's blood vessels 18, e.g., through the leg (asshown in FIG. 1) or the patient's neck. The user, guided by a real-timefluoroscopy imaging device (not shown) or other localization system,moves the electrode catheter 14 into the patient's heart 16 (as shown inmore detail in FIG. 1A).

In a preferred embodiment, the localization/mapping system is the EnSiteNavX™ navigation and visualization system of St. Jude Medical, AtrialFibrillation Division, Inc., which generates the electrical fields forlocating a catheter. Other localization systems, however, may be used inconnection with the present invention, including for example, the CARTOnavigation and location system of Biosense Webster, Inc., or the AURORA®system of Northern Digital Inc., both of which utilize magnetic fieldsrather than electrical fields. The localization and mapping systemsdescribed in the following patents (all of which are hereby incorporatedby reference in their entireties) can also be used with the presentinvention: U.S. Pat. Nos. 6,990,370; 6,978,168; 6,947,785; 6,939,309;6,728,562; 6,640,119; 5,983,126; and 5,697,377.

When the electrode catheter 14 reaches the patient's heart 16,electrodes 20 at the tip of the electrode catheter 14 may be implementedto electrically map the myocardium 22 (i.e., muscular tissue in theheart wall) and locate a target tissue 24. After locating the targettissue 24, the user must move the electrode catheter 14 into contact andelectrically couple the catheter electrode 20 with the target tissue 24before applying ablative energy to form an ablative lesion or lesions.For purposes of this application the term “contact” shall mean that theelectrode catheter is sufficiently close to the target tissue such thatit is electrically coupled to the target tissue and can transfersufficient ablation energy to form a lesion; in this sense “contact”does not require, but may include, mechanical contact.

The electrode-tissue contact refers to the condition when the catheterelectrode 14 physically touches the target tissue 24 thereby causing amechanical coupling between the catheter electrode 14 and the targettissue 24. Electrical coupling refers to the condition when a sufficientportion of electrical energy passes from the catheter electrode 14 tothe target tissue 24 so as to allow efficient lesion creation duringablation. For target tissues with similar electrical and mechanicalproperties, electrical coupling includes mechanical contact. That is,mechanical contact is a subset of electrical coupling. Thus, thecatheter electrode may be substantially electrically coupled with thetarget tissue without being in mechanical contact. In other words, ifthe catheter electrode is in mechanical contact, it is also electricallycoupled. The range or sensitivity of electrical coupling, however,changes for tissues with different electrical properties. For example,the range of electrical coupling for electrically conductive myocardialtissue is different from the vessel walls. Likewise, the range orsensitivity of electrical coupling also changes for tissues withdifferent mechanical properties, such as tissue compliance. For example,the range of electrical coupling for the relatively more compliantsmooth atrial wall is different from the relatively less compliantpectinated myocardial tissue. The level of contact and electricalcoupling are often critical to form sufficiently deep ablative lesionson the target tissue 24 without damaging surrounding tissue in the heart16. The catheter system 10 may be implemented to assess the level ofcontact (illustrated by display 11) between the electrode catheter 14and the target tissue 24, as described in more detail below.

FIG. 2a illustrates exemplary levels of electrical contact or couplingbetween an electrode catheter 14 and a target tissue 24. FIG. 2billustrates exemplary levels of mechanical contact or coupling betweenan electrode catheter 14 and a target tissue 24. Exemplary levels ofcontact or coupling may include “little or no contact” as illustrated bycontact condition 30 a, “light to medium contact” as illustrated bycontact condition 30 b, and relatively “hard contact” as illustrated bycontact condition 30 c. In an exemplary embodiment, the catheter system10 may be implemented to display or otherwise output the contactcondition for the user, e.g., as illustrated by light arrays 31 a-ccorresponding to contact conditions 30 a-c, respectively. While thelight arrays 31 a-c depict three light levels, any number of lightlevels may be used to distinguish increasing degrees of contact.

Contact condition 30 a (“little or no contact”) may be experiencedbefore the electrode catheter 14 comes into contact with the targettissue 24. Insufficient contact may inhibit or even prevent adequatelesions from being formed when the electrode catheter 14 is operated toapply ablative energy. However, contact condition 30 c (“hard contact”)may result in the formation of lesions which are too deep (e.g., causingperforations in the myocardium 22) and/or the destruction of tissuesurrounding the target tissue 24. Accordingly, the user may desirecontact condition 30 b (“light to medium contact”).

It is noted that the exemplary contact or coupling conditions 30 a-c inFIG. 2a-b are shown for purposes of illustration and are not intended tobe limiting. Other contact or coupling conditions (e.g., finergranularity between contact conditions) may also exist and/or be desiredby the user. The definition of such contact conditions may depend atleast to some extent on operating conditions, such as, the type oftarget tissue, desired depth of the ablation lesion, and operatingfrequency of the RF radiation, to name only a few examples.

FIG. 3 is a high-level functional block diagram showing the cathetersystem 10 in more detail as it may be implemented to assess contact orcoupling conditions for the electrode catheter 14. It is noted that someof the components typical of conventional tissue ablation systems areshown in simplified form and/or not shown at all in FIG. 1 for purposesof brevity. Such components may nevertheless also be provided as partof, or for use with the catheter system 10. For example, electrodecatheter 14 may include a handle portion, a fluoroscopy imaging device,and/or various other controls, to name only a few examples. Suchcomponents are well understood in the medical devices arts and thereforefurther discussion herein is not necessary for a complete understandingof the invention.

Exemplary catheter system 10 may include a generator 40, such as, e.g.,a radio frequency (RF) generator, and a measurement circuit 42electrically connected to the electrode catheter 14 (as illustrated bywires 44 to the electrode catheter). The electrode catheter 14 may alsobe electrically grounded, e.g., through grounding patch 46 affixed tothe patient's arm or chest (as shown in FIG. 1).

Generator 40 may be operated to emit electrical energy (e.g., RFcurrent) near the tip of the electrode catheter 14. It is noted thatalthough the invention is described herein with reference to RF current,other types of electrical energy may also be used for assessing contactconditions.

In an exemplary embodiment, generator 40 emits a so-called “pinging”frequency (e.g., low power) as the electrode catheter 14 approaches thetarget tissue 24. The “pinging” frequency may be emitted by the sameelectrode catheter that is used to apply ablative energy for lesionformation. Alternatively, a separate electrode catheter may be used forapplying the “pinging” frequency. In such an embodiment, the separateelectrode may be in close contact with (or affixed to) the electrode forapplying ablative energy so that a contact or coupling condition can bedetermined for the electrode which will be applying the ablative energy.

The system can be used to assess the electrode-tissue contact asdescribed in greater detail in the following applications: U.S.Application No. 60/748,234; International Application No.PCT/US06/46565; and U.S. application Ser. No. 12/096,070; each of theforegoing applications is hereby incorporated by reference in itsentirety, as if fully set forth herein. The applications explain indetail how the contact may be assessed using the phase angle componentof impedance measurements, or more simply by measuring the phase changebetween the pinging voltage signal and the pinging current signal.

The present invention can also be utilized with U.S. application Ser.No. 12/253,637, which application is hereby incorporated by reference inits entirety, as if fully set forth herein. This application describesmethods used to determine a coupling index indicative of a degree ofcontact between an electrode and a tissue wherein the coupling index iscalculated from the components of complex impedance, such as resistance,reactance, impedance magnitude, and impedance phase angle. One ofordinary skill will appreciate that the coupling index may be utilizedwith the teachings of the present invention to estimate lesioncharacteristics during lesion formation.

After the user has successfully guided the electrode catheter 14 intothe desired contact or coupling condition with the target tissue 24, agenerator, such as generator 40 or a second generator, may be operatedto generate ablative (e.g., high power) energy for forming an ablativelesion or lesions on the target tissue 24. In an exemplary embodiment,the same generator 40 may be used to generate electrical energy atvarious frequencies both for the impedance measurements (e.g., “pinging”frequencies) and for forming the ablative lesion. In alternativeembodiments, however, separate generators or generating units may alsobe implemented without departing from the scope of the invention.

In an exemplary embodiment, measurement circuit 42 may be operativelyassociated with a processor 50 and memory 52 to analyze the measuredimpedance. By way of example, processor 50 may determine a phase angle,and based on the phase angle, the processor 50 may determine acorresponding contact or coupling condition for the electrode catheter14. In an exemplary embodiment, contact or coupling conditionscorresponding to various phase angles may be predetermined, e.g., duringtesting for any of a wide range of tissue types and at variousfrequencies. The contact or coupling conditions may be stored in memory52, e.g., as tables or other suitable data structures. The processor 50may then access the tables in memory 52 and determine a contact orcoupling condition corresponding to impedance measurements based on thereactance component and/or phase angle. The contact or couplingcondition may be output for the user, e.g., at display device 54.Processor 50 may comprise a conventional general purpose computer, aspecial purpose computer, a distributed computer, or any other type ofcomputer. Processor 50 may comprise one or more processors, such as asingle central-processing unit, or a plurality of processing units,commonly referred to as a parallel processing environment.

Although impedance measurements may be used to determine the phaseangle, in an alternative embodiment, the measurement circuit 42 may beimplemented as a phase detection circuit to directly determine the phaseangle. An exemplary phase detection circuit 80 is shown in FIG. 5 in ahigh-level functional block diagram. Phase detection circuit 80 is shownand described with reference to its functional components. It is notedthat a particular hardware configuration is not necessary for a fullunderstanding of the invention. Implementation of the phase detectioncircuit 80 in digital and/or analog hardware and/or software will bereadily apparent to those having ordinary skill in the electronics artafter becoming familiar with the teachings herein.

Exemplary phase detection circuit 80 may include a current sensor 82 andvoltage sensor 84 for measuring current and voltage at theelectrode-tissue interface. The current and voltage measurements may beinput to a phase comparator 86. Phase comparator 86 provides a directcurrent (DC) output voltage proportional to the difference in phasebetween the voltage and current measurements.

Optionally, current measurements may be phase shifted by phase shiftcircuit 88 to facilitate operation of the phase comparator 86 by“correcting” phase lag between the measured current and the measuredvoltage. Also optionally, output from the phase comparator 86 may be“corrected” by phase adjustment circuit 90 to compensate for externalfactors, such as the type of grounding patch 46 being used. A signalscaling circuit 92 may also be provided to amplify the output (e.g.,from milli-volts to volts) for use by various devices (e.g., theprocessor 50 and display device 54 in FIG. 3).

It is noted that phase detection circuit 80 shown in FIG. 5 is providedas one example, and is not intended to be limiting. Otherimplementations may also be readily provided by those having ordinaryskill in the electronics arts after becoming familiar with the teachingsherein without departing from the scope of the invention.

In another exemplary embodiment, measurement circuit 42 as depicted inFIG. 3 includes circuitry to measure voltage and current for differenttypes of power supplies that are used to assess contact between thecatheter and tissues being treated.

Measurement circuit 42 also includes temperature measurement circuitsthat are used to measure and monitor the temperature of the tissue beingtreated. Measurement circuit 42 utilizes previously described circuitryand/or additional circuitry to measure and monitor power that isdelivered by generator 40 and/or by ablation catheter 20.

In an exemplary embodiment, measurement circuit 42 is operativelyassociated with a processor 50 and memory 52 to analyze degrees ofcontact or coupling, temperature changes, power and energy. In anexemplary embodiment, processor 50 is programmed to perform regressionanalysis as described below. Display device 54 may be used to providefeedback to the operator in graphical or numerical form. For example,processor 50 may calculate and display on display device 54 the volumeof a lesion as it is being formed. Display device may also display atarget lesion volume so that the target may be compared to the size ofthe lesion being formed. Preferably, processor 50 is programmed todisplay tissue temperature and to deactivate the ablation power sourcewhen the tissue temperature reaches a desired temperature for lesionformation (e.g., about 50-55° C.).

In tissue ablation, a thermal lesion is created when the tissueundergoes coagulation necrosis at temperatures above about 55° C. Inradiofrequency (RF) ablation, lesion formation depends upon a number ofparameters, such as: (i) electrode-tissue electrical coupling; (ii) theamount of power applied to the electrode from the RF generator; (iii)the duration of power being applied to the electrode by the RFgenerator; and (iv) the thermal properties and effects of aspects suchas (a) the electrode; (b) the tissue; and (c) the fluid around theelectrode.

For purposes of this application, “lesion size” is intended to refer tothe volume of the lesion being created, and more particularly, thevolume of the tissue that underwent coagulation necrosis. Thus, the term“lesion size” is used interchangeably with “lesion volume.”

The electrical coupling between the electrode and the tissue refers tothe fraction of the electrical energy that flows from the electrode intothe tissue. Electrical coupling is effected by: (i) the electrodeproximity to or mechanical contact with the tissue; (ii) the size (e.g.,surface area) of the electrode; and (iii) the electrical properties of:(a) the electrode; (b) the tissue; and (c) the fluid around theelectrode.

Creation of thermally mediated lesion using RF current in tissue isgenerally described by the bio-heat transfer equation, which in itssimplified form may be written as,

${\rho\; c\frac{\partial T}{\partial t}} = {{{\nabla{\cdot k}}{\nabla T}} + {JE} - Q_{h}}$where:

-   -   JE is the specific absorption rate (“SAR”) of energy applied to        the tissue;    -   ∇·k∇T is the thermal diffusion effect due to thermal        conductivity of the tissue;    -   Q_(h) is the rate of thermal energy transfer due the convective        effects, such as perfusion, blood flow, irrigated cooling;    -   ρc ∂T/∂t is rate of energy accumulation in the tissue, which        causes the tissue temperature to increase;    -   T is the tissue temperature;    -   ρ is the tissue density;    -   c is the specific heat capacity of the tissue;    -   ∂T/∂t is the rate of change in tissue temperature;    -   J is the electric current density within the tissue;    -   E is the electric field intensity within the tissue.

The current density J is defined asJ=i/A,where:

-   -   i is the RF current;    -   A is the area normal to the flow of the current, and is the        effective area of electrical coupling between the electrode and        tissue.

J is related to the electric field E as,J=−σ∇V=σE,where:

-   -   σ is the electrical conductivity of the medium;    -   V is the electrical potential; and    -   ∇V is the gradient of electrical potential.

Alternately, SAR may be rewritten as

$\begin{matrix}{{J\; E} = {{J}^{2}/\sigma}} \\{= {i^{2}/{\left\lbrack {A^{2}\sigma} \right\rbrack.}}}\end{matrix}$

Thus an estimation of SAR depends upon the RF current i, the effectivearea A, and electrical conductivity σ. In energy dosimetry applicationsof RF ablation, the electrical conductivity σ is a tissue property thatis generally known, the RF current i is readily measurable, but A is notreadily measurable. The difficulty in measuring A in catheter-basedcardiac ablation application is further compounded by: the compliance ofthe tissue when the catheter is in physical contact with the heart wall;and the contour of the tissue, such as trabeculated tissue, when theelectrode may not necessarily be in physical contact with the heartwall.

The phase angle method of measuring electrical coupling provides thereactance X_(R) of the tissue to the application of RF energy:X _(R)=1/(2πfC)where:

-   -   f is frequency    -   C is capacitance, which for parallel plate capacitors is given        as        C=εA/d        where:    -   ε is permittivity of the medium between the plates    -   A is the cross sectional area between the plates    -   d is the distance between the plates.

When the electrode is in contact with or close to the tissue, ε may betaken as the permittivity of the tissue, d may be approximated as thedepth in tissue that yields enough strength of the RF field so as tocreate a lesion. In that respect, A may be taken as the effective areaof electrical coupling.

The contact or coupling area is an important parameter in RF ablation.It determines: (i) the current density and energy density at theelectrode-tissue interface; and (ii) the portion of RF energy absorbedin the tissue during ablation. High current density and energy densityat the electrode-tissue interface increase the susceptibility tocoagulum and thrombus formation. Excessive energy absorption leads totissue charring and increases the risk of perforation.

A measure of electrode contact or coupling area, therefore, has primeclinical significance in RF ablation. Such information will allowcustomizing ablation parameters at individual sites by titrating powerlevels and ablation time necessary to create safe lesions.

A technical advantage of the present invention is to provide lesion sizefeedback to physicians based on the degree of electrode-tissue contactor coupling, the RF power levels being delivered to the tissue, and theduration of the RF ablation treatment.

Another technical advantage of the present invention is to providelesion feedback on lesion characteristics to physicians based onelectro-physiological changes in the tissue as measured during the RFablation treatment.

In one embodiment, the present invention comprises an ablation cathetersystem that permits electrical contact sensing. The catheter systemincludes:

-   -   (i) Circuit to measure RF current signal;    -   (ii) Circuit to measure RF voltage signal; and    -   (iii) Circuit to measure phase angle between current and        voltage.

The present invention determines the degree of contact sensing based onthe measurement of phase angle Δφ between the RF voltage signal and theRF current signal or the complex impedance as measured using themeasured voltage and current. The phase angle Δφ changes with the levelof electrode-tissue contact. Preferably, the phase angle Δφ between theRF voltage signal and the RF current signal is measured before orshortly after the RF energy source is activated, though the phase angleΔφ can be measured at any point in time and be used to assess varyingdegrees of contact. The phase angle Δφ also changes with tissuetemperature, and so, as more ablation energy is delivered to the tissue,reliance upon changes in phase angle Δφ must take into consideration theeffect of the increased tissue temperature. Generally speaking, themagnitude of phase angle Δφ increases as the degree of tissue-electrodecontact increases.

The RF voltage signal being used to measure the phase angle may besupplied by the same RF power source that provides the ablation energyor may be provided by a separate independent supply. The frequency ofthe RF energy used to assess the electrical coupling is preferablybetween about 1 KHz and about 1000 KHz, and more preferably betweenabout 50 KHz and about 500 KHz, and most preferably between about 400KHz and about 500 KHz. The power of the RF signal needed to assesselectrical coupling is much lower than the power levels required forablation, and preferably is less than about 1 W, and more preferablyless than about 0.001 W. The current amperage is also significantly lessthan is necessary for effective ablation and is preferably less than 10mA, and more preferably less than about 1 mA.

An alternative approach to the device describe above that determinesphase angle by comparing the voltage signal to the current is to use acircuit that measures the complex impedance, which is the complex sum ofresistance and reactance. The phase angle of the complex impedance isthe same phase angle that would be measured by comparing the voltagesignal to the current signal.

Yet another alternative approach to the device described above thatdetermines phase angle by comparing the voltage signal to the current isto use a circuit that measures a coupling index which is calculated fromthe measured components of complex impedance, such as resistance,reactance, impedance magnitude, and impedance phase angle.

It is contemplated that mechanical contact sensing and/orelectromechanical sensing may be utilized in conjunction with theelectrical contact sensors described above, including for example,piezoelectric sensors, PVDF (polyvinylidene fluoride) film basedsensors, and fiber optic-based opto-mechanical contact sensors. In thecase of an electrode that senses contact with a beating heart wall, theelectrode sensor generates a dynamic voltage signal. The dynamic voltagesignal obtained from these contact sensors exhibit waveformcharacteristics similar to the EKG signals that cause myocardialcontractions. It is also contemplated that piezoresistive sensors andQuantum Tunneling Composite (QTC) based sensors may be used, where theresistance of the sensor changes with the contact pressure of theelectrode with the tissue.

Contact sensing is important to the ablation process because delivery ofablation energy is proportional to improved electrode-tissue contact. Inother words, electrode-tissue contact dictates the energy absorption intissue, and it is energy absorption in tissue that results in anincrease in tissue temperature. As discussed above, a goal of ablationtreatment is to increase the tissue temperature to a point that createsirreversible electro-physiological changes in the tissue in theformation of a lesion. Lesion formation in tissues by thermo-therapeuticmeans is achieved by maintaining the tissue temperature above about 50°C.

The total energy ξ_(a) in Joules applied by the RF generator at power PWatts for a duration of t_(e) seconds isξ_(a) =P×t _(e)  (1)

When this energy is applied to an electrode in an endocardialapplication, part of this energy, ξ_(t), is absorbed into the tissue tocreate the lesion at the target site, while the remainder of the energy,ξ_(b), is lost to the surrounding blood, tissue, electrolyte, and/or theelectrode:ξ_(a)=ξ_(t)+ε_(b)  (2)

Alternatively, the portion of applied energy ξ_(a) absorbed in thetissue ξ_(t) may be expressed asξ_(t)=αξ_(a)  (3)where α is an absorptivity factor with a numerical value between 0 and1, such that α=0 when all the applied energy is lost without anyabsorption in the tissue; α=1 when all the energy is absorbed in thetissue.

As the energy ξ_(t) is absorbed into the tissue, the temperature of thetissue increases. The energy required to create a lesion of volume v_(l)may be estimated from

$\begin{matrix}\begin{matrix}{\xi_{t =}\rho_{l} \times v_{l} \times c_{l} \times \Delta\; T} \\{\approx {\rho_{l} \times v_{l} \times c_{l} \times \left( {T_{l} - 37} \right)}}\end{matrix} & (4)\end{matrix}$where ρ_(l) is the density of the tissue; c_(l) is the tissue specificheat at constant pressure; ΔT is the temperature rise required to causetissue ablation; T_(l) is the temperature for coagulation necrosis andis also the tissue temperature at the lesion boundary. The patient'sbody temperature is 37° C. prior to application of ablation energy.

Expressed in terms of the lesion volume v_(l), Eq. (4) becomes

$\begin{matrix}\begin{matrix}{v_{l} = \frac{\xi_{t}}{\rho_{l} \times c_{l} \times \Delta\; T}} \\{\approx \frac{\xi_{t}}{\rho_{l} \times c_{l} \times \left( {T_{l} - 37} \right)}}\end{matrix} & (5)\end{matrix}$

Substituting ξ_(t) from Eq. (3) into Eq. (5)

$\begin{matrix}\begin{matrix}{v_{l} = \frac{{\alpha\xi}_{a}}{\rho_{l} \times c_{l} \times \Delta\; T}} \\{\approx \frac{{\alpha\xi}_{a}}{\rho_{l} \times c_{l} \times \left( {T_{l} - 37} \right)}}\end{matrix} & (6)\end{matrix}$

Substituting ξ_(a) from Eq. (1) into Eq. (6)

$\begin{matrix}\begin{matrix}{v_{l} = \frac{\alpha\left( {P \times t_{e}} \right)}{\rho_{l} \times c_{l} \times \Delta\; T}} \\{\approx \frac{\alpha\left( {P \times t_{e}} \right)}{\rho_{l} \times c_{l} \times \left( {T_{l} - 37} \right)}}\end{matrix} & (7)\end{matrix}$

For myocardial tissue ρ_(l)=1200 kg·m⁻³, c_(l)=3200 J·kg⁻¹·°C.⁻¹. Takingthe T_(l)=55° C., the temperature rise required to cause tissue ablationis ΔT≈(55−37)° C., or simply, 18° C. Eq. (7) then reduces to:

$\begin{matrix}\begin{matrix}{v_{l} = {\frac{\alpha\left( {P \times t_{e}} \right)}{1200 \times 3200 \times 18}m^{3}}} \\{\approx {\frac{\alpha\left( {P \times t_{e}} \right)}{69.12 \times 10^{6}}m^{3}}} \\{\approx {14.47\left( {\alpha \times P \times t_{e}} \right){mm}^{3}}}\end{matrix} & (8)\end{matrix}$

Eq. (8) shows that the main variables determining lesion volume are (i)power P, (ii) duration t_(e), and (iii) absorptivity factor α.

The absorptivity factor α depends upon a number of factors that mainlyinclude (i) the degree of electrode-tissue contact ζ, (ii) tissuecharacteristics χ, and (iii) ambient flow conditions ℑ at the site ofthe contact:

$\begin{matrix}\begin{matrix}{\alpha = {f\begin{Bmatrix}{\left. {{Electrode}\text{-}{tissue}\mspace{14mu}{contact}} \right),\left( {{Tissue}\mspace{14mu}{characteristics}} \right),} \\{\left( {{Flow}\mspace{14mu}{conditions}} \right),\ldots}\end{Bmatrix}}} \\{= {f\begin{Bmatrix}{\zeta,} & {\chi,} & {\mathcal{F},} & \ldots\end{Bmatrix}}}\end{matrix} & (9)\end{matrix}$

In the absorptivity factor, tissue characteristics and ambient flowconditions at the site of the electrode-tissue contact are physiologicalparameters. On the other hand, level of contact between the electrodeand the tissue is established by the physician, and is, therefore,operator dependent.

Limiting the dependency of the lesion volume to operator dependentvariables, Eq. (8) can be rewritten to include the aspects of contactsensing as:v _(l)≈14.47[f ₁(ζ)×P×t _(e)]mm ³  (10)where 0≦f₁(ζ)≦1.

For RF energy applications, phase change Δφ between the voltage andcurrent is directly related to the level of electrode-tissue contactΔφ

ζ  (11)

The lesion volume can then be related to phase change Δφ due toelectrode-tissue contact asv _(l)≈14.47[f ₂(Δφ)×P×t _(e)]mm³  (12)where 0≦f₂(Δφ)≦1.

Eq. (12) shows that the lesion volume v_(l) is a function of threevariables:

-   -   (i) phase change Δφ due to electrode-tissue contact ζ;    -   (ii) power P; and    -   (iii) duration t_(e).

To determine the functional dependence of any one variable on lesionvolume v_(l) will require multiple data points as part of a validationstudy. Preferably, the validation study is created using a plurality oflesions in which information may be gained to permit estimation apriori. For ease of concept, a plurality of lesions can be made usingvarious different levels of contact as follows:

-   -   Preset power P, i.e. in the power control mode;    -   Preset duration t_(e); and    -   Different levels of contact, such as Δφ₁, Δφ₂, . . . Δφ_(n).

As part of the validation study, the ablation system may be operated inpower control mode, in which the ablation energy is delivered at a fixedpower level. Each of the plurality of different levels of contact isdetermined by measuring the phase angle Δφ between the RF voltage signaland the RF current signal at a point in time before or shortly after theRF energy source is activated. If the phase angle is measured before thecommencement of ablation energy, the changes in phase angle can be moreeasily compared across the plurality of lesions because each is measuredat the same tissue temperature. While the phase measurement may be madeshortly after the ablation energy is activated, the measurement ispreferably made before any appreciable increase in temperature. Becausethe phase angle Δφ varies with changes in tissue temperature, once theablation energy begins to cause an increase in tissue temperature, theimpact on the phase angle as a measure of electric coupling will requireadjustments.

Generally speaking, in this set-up, only one variable is changing overthe creation of the plurality of different lesions, namely the degree ofcontact (which causes a variation in the phase angle). At the end ofeach ablation process, for each of the plurality of lesions:

-   -   Lesion volume v_(l) is measured;    -   Values of v_(l), P, and t_(e) are substituted in Eq. (12) to        obtain the value of f₂(Δφ); and    -   Values of f₂(Δφ) are plotted against Δφ and a regression curve        f_(2R)(Δφ) is computed.

The volume v_(l) is measured using known volumetric measurements. Forexample, in the case of a hypothetical rectangular lesion, volume may bedetermined by multiplying width by length by depth. Depending on theshape, other formulas and/or measurements may be made using knownvolumetric techniques. Typically, the length and width of the lesion arein proportion to the electrode size, and accordingly, a lesion depth maybe estimated using lesion length and lesion width.

The collection of data points for the validation study is preferablygenerated, preferably, using a plurality of similar tissue samples. Ofcourse, the tissue samples may be from the same human, multiple humansand/or non-humans. In addition, while the validation study may becompleted in advance, the validation study (as well as any regressionanalysis of the underlying data) may continually be updated usingadditional data points as they are collected. As one example, thevalidation study may utilize several hundred data points performed in apre-clinical animal study, upon which a regression analysis may beperformed; additional data points may be added to the study as theadditional data points are collected, and the associated regressionanalysis may be continually updated.

A graph or lookup table for f₂(Δφ) can be generated using a knownregression analysis techniques that can be run on the plurality of datapoints previously collected; the resulting graph of lookup table isreferred to as regression curve f_(2R)(Δφ) or, more simply, f_(2R)(Δφ).The f_(2R)(Δφ) data can then be used to provide lesion size feedback inreal-time for various power settings such as power control modeoperations for various levels of contact or coupling.

For example, once the regression analysis has been completed, lesionsize feedback can be provided on future ablation treatment. An ablationcatheter may be placed in contact with tissue to be treated, and thedegree of electrical coupling can be determined by measuring the phasechange Δφ between the voltage and current curves as described above.Using the f_(2R)(Δφ) data embodied in the regression curve, the measuredΔφ can be used to determine a value of f₂(Δφ). The determined valuef₂(Δφ) can then be substituted into Eq. (12), along with the value ofpower P, to estimate the size of lesion development v_(l) as a functionof time. This methodology is useful for providing lesion size feedbackthroughout the ablation process.

The characteristics of a lesion formed during ablation depends upon theelectro-physiological changes that occur in the tissue during theablation process, including for example, the temperature attained by thetissue. The combination of lesion size feedback and tissue temperatureis most useful to increasing the efficacy of an ablation treatment, andthe present invention provides real-time feedback on the characteristicsof the lesion being formed as the surgeon performs the ablation process.

In an exemplary embodiment of the present invention, an ablationcatheter of the ablation system is placed in contact with tissue to betreated at a particular level of contact. The degree of contact isdetermined by applying a first power signal and then measuring the phaseangle between the voltage signal and the current signal; alternativelythe degree of contact may be determined by measuring the compleximpedance using the applied first power signal, and in particular, usingthe phase angle associated with the complex impedance. Ablation energyis then delivered at the same degree of contact to create a lesion, andthe system estimates on a real-time basis the size and othercharacteristics of the lesion being created by using at least thefollowing: i) information obtained through regression analysis; ii)information related to the degree of contact; iii) information relatedto the power of ablation energy being delivered; and iv) the amount oftime for which the ablation energy has been activated. Optionally, thelesion volume of the lesion being created may be estimated and thetreatment time period (for which ablation energy is to be applied) isadjusted based on the estimated lesion volume in an effort to achieveparticular lesion characteristics. For example, adjustments may be madeto the ablation power source in order to slow the delivery of ablationenergy to help reduce the risk of tissue pop.

While the degree of contact is preferably measured before anysignificant increase in temperature from the delivery of ablation energy(for example, by measuring before the ablation energy is activated), itis contemplated that the degree of contact may be measured throughoutthe ablation process. Of course, to compare degrees of contact willrequire adjustments based on changes in tissue temperature. Generallyspeaking, the phase angle associated with a particular degree of contactwill reduce in magnitude as the temperature of the tissue increases.

Accounting For Changes In Tissue Temperature.

Preliminary in vitro studies show that at any contact level, phase angleis also affected by changes in tissue temperature. In other words, phaseangle change is a function of tissue temperature as well as electricalcoupling—the latter of which was discussed in detail above:Δφ=Δφ(ζ,ΔT).  (12)

Including such effects, Eq. (7) can be recast in a form indicative ofelectro-physiologic changes in the lesion volume v_(l) obtained bysubjecting the tissue to a temperature increase ΔT; thus

$\begin{matrix}{v_{l} = \frac{f_{2}\left\{ {\Delta\;{\varphi\left( {\zeta,{\Delta\; T}} \right)}} \right\} \times P \times t}{\rho_{l} \times c_{l} \times \Delta\; T}} & (14)\end{matrix}$

In Eq. (14) the lesion volume v_(l) is volume of the tissue thatunderwent coagulation necrosis; P is the applied power; t is theduration; ρ_(t) is the density of the tissue; c_(l) is the tissuespecific heat at constant pressure; ΔT is the rise in tissue temperatureobtained during ablation.

While the previous discussion utilized a fixed power P (such as willoccur in a power-controlled mode of ablation), another embodiment of thepresent invention may be utilized with varying levels of power, such asmay occur in a temperature-controlled mode of ablation. In thisembodiment, the equations may be modified to account for variations inpower as a function of time (which will be adjusted by using thefunction P(t)). This introduces another variable into the system ofequations, which variable requires adjustments in the equations.

Under temperature control mode, the applied power P is generally notconstant but varies with time when the preset maximum power is higherthan needed to attain the tissue temperature. In that case, the totalenergy ξ_(a) applied by the RF generator cannot be expressed as P×t_(e).Instead, ξ_(a) is obtained from the time integral of P as

$\begin{matrix}{\xi_{a} = {\int_{0}^{t_{e}}{{P(t)}{\mathbb{d}t}}}} & (15)\end{matrix}$

Rewriting Eq. (14) for temperature control mode operation

$\begin{matrix}\begin{matrix}{v_{l} = \frac{f_{2}\left\{ {{\Delta\varphi}\left( {\xi,{\Delta\; T}} \right)} \right\} \times \xi_{a}}{\rho_{l} \times c_{l} \times \Delta\; T}} \\{= {\frac{f_{2}\left\{ {{\Delta\varphi}\left( {\xi,{\Delta\; T}} \right)} \right\} \times {\int_{0}^{t_{e}}{{P(t)}{\mathbb{d}t}}}}{3.84 \times 10^{6} \times \Delta\; T}m^{3}}} \\{= {\frac{260.4 \times f_{2}\left\{ {{\Delta\varphi}\left( {\xi,{\Delta\; T}} \right)} \right\} \times {\int_{0}^{t_{e}}{{P(t)}{\mathbb{d}t}}}}{\Delta\; T}{mm}^{3}}}\end{matrix} & (16)\end{matrix}$In Eq. (16), ΔT=(T_(set)−37)° C., where T_(set) is the presettemperature in the temperature control mode; t_(e) is the duration atthe instant when the recorded temperature T first attains T_(set).

Eq. (16) shows that the lesion volume v_(l) is a function of fourvariables:

-   -   (i) temperature rise ΔT    -   (ii) phase change Δφ due to electrode-tissue contact ζ    -   (iii) phase change Δφ due to temperature rise ΔT    -   (iv) total applied energy ξ_(a)

To determine the functional dependence of any one variable on lesionvolume v_(l) will require multiple data points as part of a validationstudy. Preferably, the validation study is created using a plurality oflesions in which information may be gained to permit estimation apriori. For ease of concept, a plurality of lesions can be made usingvarious different levels of contact as follows:

-   -   Preset cutoff temperature T_(set), i.e. in the temperature        control mode    -   Preset maximum power P_(max)    -   Different levels of contact, such as Δφ₁, Δφ₂, . . . Δφ_(n)

At the end of the creation of each of the plurality of lesions:

-   -   At t=t_(e), phase change Δφ (ΔT)=Δφ|_(t=te) due to temperature        rise ΔT=(T_(set)−37° C. is recorded    -   Lesion volume v_(l) is measured    -   Values of v_(l), P(t), t_(e), and ΔT are substituted in Eq. (16)        to obtain the value of f₂(Δφ)    -   Values of f₂(Δφ) are plotted against Δφ(ζ)=Δφ|_(t=0) and ΔT to        compute the regression curve f_(2R)[Δφ(ζ, ΔT)]

The volume v_(l) is measured using known volumetric measurements. Forexample, in the case of a hypothetical rectangular lesion, volume may bedetermined by multiplying width by length by depth. Depending on theshape, other formulas and/or measurements may be made using knownvolumetric techniques. Typically, the length and width of the lesion arein proportion to the electrode size, and accordingly, a lesion depth maybe estimated using lesion length and lesion width.

The collection of data points for the validation study is preferablygenerated, using a plurality of similar tissue samples. Of course, thetissue samples may be from the same human, multiple humans and/ornon-humans. In addition, while the validation study may be completed inadvance, the validation study (as well as any regression analysis of theunderlying data) may continually updated using additional data points asthey are collected. As one example, the validation study may utilizeseveral hundred data points performed in a pre-clinical animal study.

A graph or lookup table for f₂[Δφ(ζ, ΔT)] can be generated using a knownregression analysis techniques that can be run on the plurality of datapoints previously collected; the resulting graph of lookup table isreferred to as regression curve f_(2R)[Δφ(ζ, ΔT)] or, more simply,f_(2R)[Δφ(ζ, ΔT)]. The f_(2R)[Δφ(ζ, ΔT)] data can then be used toprovide lesion size feedback in temperature control mode operations forvarious levels of contact or coupling.

For example, once the regression analysis has been completed, lesionsize feedback can be provided on future ablation treatment. An ablationcatheter may be placed in contact with tissue to be treated, and thedegree of electrical coupling can be determined by measuring the phasechange Δφ between the voltage and current curves as described above.Using the f_(2R)[Δφ(ζ, ΔT)] data embodied in the regression curve, themeasured Δφ can be used to determine a value of f₂[Δφ(ζ, ΔT)]. Thedetermined value f₂[Δφ(ζ, ΔT)] can then be substituted into Eq. (16),along with the monitored information on P(t) and ΔT to estimate the sizeof lesion development v_(l) as a function of time. This methodology isuseful for providing lesion size feedback throughout the ablationprocess.

In an exemplary embodiment of the present invention, an ablationcatheter of the ablation system is placed in contact with tissue to betreated at a particular level of contact. The degree of contact isdetermined by applying a first power signal and then measuring the phaseangle between the voltage signal and the current signal; alternativelythe degree of contact may be determined by measuring the compleximpedance using the applied first power signal, and in particular, usingthe phase angle associated with the complex impedance. Ablation energyis then delivered at the same degree of contact to create a lesion usinga mode of operation in which the ablation power level may vary overtime. The system estimates on a real-time basis the size and othercharacteristics of the lesion being created by using at least thefollowing: i) information obtained through regression analysis; ii)information related to the degree of contact; iii) information relatedto the total amount of ablation energy being delivered over time,including variations of power over time; and iv) the amount of time forwhich the ablation energy has been activated. Optionally, the estimationmay be based, in part, on changes in tissue temperature, and changes inphase angle due to changes in tissue temperature. The lesion volume ofthe lesion being created may be estimated and the treatment time period(for which ablation energy is to be applied) may be adjusted based onthe estimated lesion volume in an effort to achieve particular lesioncharacteristics. For example, adjustments may be made to the ablationpower source in order to slow the delivery of ablation energy to helpreduce the risk of tissue pop.

In an exemplary embodiment of the present invention, a system may beused to estimate treatment times to achieve a lesion having certaincharacteristics, for example, a lesion with a particular depth.

In another exemplary embodiment of the present invention, a system maybe used to estimate lesion characteristics for a given treatment timeperiod. For example, lesion depth may be estimated in real time usingthe time for which an ablation treatment has been on-going. As discussedabove, lesion volume may be estimated as a function of time (namely, thetime for which an ablation treatment has been active). Also as discussedabove, the length and width of the lesion are in proportion to theelectrode size, and can be estimated for any given electrode shape. Oncethe width and length has been estimated for an electrode (for example,but using a regression analysis on detailed volumetric measurementswhich include, width, length, depth and a shape factor), lesion depthmay be estimated on a real-time basis.

While the degree of contact is preferably measured before anysignificant increase in temperature from the delivery of ablation energy(for example, by measuring before the ablation energy is activated), itis contemplated that the degree of contact may be measured throughoutthe ablation process.

One of ordinary skill will appreciate that the coupling index describedin U.S. application Ser. No. 12/253,637, referenced and incorporatedabove, may also be utilized with the teachings of the present inventionto estimate absorptivity factor (α). The coupling index can becalculated from the components of complex impedance, such as resistance,reactance, impedance magnitude, and impedance phase angle, and can beused to estimate absorptivity as described above. Once an absorptivityfactor (α) has been estimated, the absorptivity can be used to estimatelesion characteristics, including for example, lesion volume (includingwidth, length, and depth) as well as to estimate time needed to completetreatment in order to achieve lesions having certain characteristics.

While the power source used for ablation is described in certainembodiments above as being an RF power source, the principles of thepresent invention are applicable to other power sources.

While the power source used for assessing tissue-electrode contact isdescribed in certain embodiments above as being an RF power source, theprinciples of the present invention can be used with any alternatingcurrent power source, including very low frequency, low frequency andhigh frequency power sources. It is anticipated that the circuitsdescribe above may be modified to accommodate the changes in frequencyand to filter out noise that may otherwise be present.

Although several embodiments of this invention have been described abovewith a certain degree of particularity, those skilled in the art couldmake numerous alterations to the disclosed embodiments without departingfrom the spirit or scope of this invention.

All directional references (e.g., upper, lower, upward, downward, left,right, leftward, rightward, top, bottom, above, below, vertical,horizontal, clockwise, and counterclockwise) are only used foridentification purposes to aid the reader's understanding of the presentinvention, and do not create limitations, particularly as to theposition, orientation, or use of the invention. Joinder references(e.g., attached, coupled, connected, and the like) are to be construedbroadly and may include intermediate members between a connection ofelements and relative movement between elements. As such, joinderreferences do not necessarily infer that two elements are directlyconnected and in fixed relation to each other. It is intended that allmatter contained in the above description or shown in the accompanyingdrawings shall be interpreted as illustrative only and not limiting.Changes in detail or structure may be made without departing from thespirit of the invention as defined in the appended claims.

What is claimed is:
 1. An ablation control system, comprising: ameasurement circuit to determine a contact state between an ablationelectrode and a tissue to be ablated by measuring a degree of electricalcoupling between the ablation electrode and the tissue to be ablated; aclock to measure a time period during which ablative energy is appliedby the ablation electrode to the tissue to be ablated; a lesion analysisprocessor for estimating a volume of a lesion forming in the tissue tobe ablated as a function of at least three interdependent variables,wherein the at least three interdependent variables are inverselyrelated for a preset volume of the lesion forming in the tissue to beablated, and wherein the at least three interdependent variablescomprise: the contact state between the ablation electrode and thetissue to be ablated, as measured by the measurement circuit; a powerlevel at which the ablation electrode applies ablative energy to thetissue to be ablated; the measured time period during which the ablationelectrode applies ablative energy to the tissue to be ablated; and acontroller coupled to the lesion analysis processor and configured tocontrol an ablation power source to create a lesion of the preset volumebased on information provided by the lesion analysis processor.
 2. Theablation control system according to claim 1, wherein the measurementcircuit determines the degree of electrical coupling between theablation electrode and the tissue to be ablated using phase angles. 3.The ablation control system according to claim 2, wherein themeasurement circuit comprises a phase detection circuit.
 4. The ablationcontrol system according to claim 2, wherein the measurement circuitcomprises: a voltage measurement device for measuring a voltage signalbeing delivered to the tissue to be ablated; a current measurementdevice for measuring a current signal being delivered to the tissue tobe ablated; and a phase measurement device to determine an amount ofphase change between the measured voltage signal and the measuredcurrent signal.
 5. The ablation control system according to claim 1,further comprising a tissue temperature sensor to measure a temperatureof the tissue to be ablated, and wherein the controller is furthercoupled to the tissue temperature sensor such that, if the temperatureof the tissue to be ablated exceeds a maximum desirable temperature, thecontroller sends a deactivation signal to the ablation power source. 6.The ablation control system according to claim 1, wherein: the lesionanalysis processor utilizes a regression analysis of a plurality ofpreviously collected data points, and each of the plurality ofpreviously collected data points comprises information respectively fora plurality of lesions, including at least a degree of electricalcoupling, a lesion volume, and an ablation power level.
 7. A method ofablating tissue in need of treatment, comprising: delivering ablativepower to the tissue in need of treatment via an ablation catheter havingat least one electrode coupled to a programmable power source; using alesion analysis processor, estimating a volume of a lesion forming inthe tissue in need of treatment as a function of at least threeinterdependent variables, wherein the at least three interdependentvariables are inversely related for a preset volume of the lesionforming in the tissue to be ablated, and wherein the at least threeinterdependent variables comprise: a contact state between the ablationcatheter and the tissue in need of treatment, as determined by measuringa degree of electrical coupling between the ablation catheter and thetissue in need of treatment; a power level at which the programmablepower source delivers ablative power to the tissue in need of treatment;and a measured time period over which ablative power is delivered to thetissue in need of treatment; and controlling the programmable powersource based on information provided by the lesion analysis processor toa create a lesion having the preset volume.
 8. The method according toclaim 7, wherein the lesion analysis processor determines the degree ofelectrical coupling between the ablation catheter and the tissue in needof treatment using phase angles.
 9. The method according to claim 8,wherein the lesion analysis processor determines an amount of phasechange between a measurement of a voltage signal being delivered to thetissue in need of treatment and a measurement of a current signal beingdelivered to the tissue in need of treatment.
 10. The method accordingto claim 7, wherein the lesion analysis processor utilizes a regressionanalysis of a plurality of previously collected data points, and each ofthe plurality of previously collected data points comprises informationrespectively for a plurality of lesions, including at least a degree ofelectrical coupling, a lesion volume, and an ablation power level. 11.The method according to claim 7, further comprising: measuring atemperature of the tissue in need of treatment while delivering ablativepower thereto; and sending a signal from the controller to theprogrammable power unit to disable the programmable power unit if themeasured temperature of the tissue in need of treatment exceeds amaximum desirable temperature.
 12. An ablation control system,comprising: a measurement circuit to determine a contact conditionbetween an ablation electrode and a tissue to be ablated; a clock tomeasure a time period during which ablative energy is applied by theablation electrode to the tissue to be ablated; a lesion analysisprocessor for estimating a volume of a lesion forming in the tissue tobe ablated as a function of at least three interdependent variablescomprising: the determined contact condition between the ablationelectrode and the tissue to be ablated; a power level at which theablation electrode applies ablative energy to the tissue to be ablated;the measured time period during which the ablation electrode appliesablative energy to the tissue to be ablated; and a controller coupled tothe lesion analysis processor and configured to control an ablationpower source to form a lesion having a preset volume in the tissue to beablated based on information provided by the lesion analysis processor,wherein the at least three interdependent variables are related for thepreset volume according to an equation that approximates lesion volumeas a product of the at least three interdependent variables.
 13. Theablation control system according to claim 12, wherein the measurementcircuit determines a degree of electrical coupling between the ablationelectrode and the tissue to be ablated.
 14. The ablation control systemaccording to claim 13, wherein the measurement circuit determines thedegree of electrical coupling between the ablation electrode and thetissue to be ablated using phase angles.
 15. The ablation control systemaccording to claim 14, wherein the measurement circuit comprises a phasedetection circuit.
 16. The ablation control system according to claim14, wherein the measurement circuit comprises: a voltage measurementdevice for measuring a voltage signal being delivered to the tissue tobe ablated; a current measurement device for measuring a current signalbeing delivered to the tissue to be ablated; and a phase measurementdevice to determine an amount of phase change between the measuredvoltage signal and the measured current signal.
 17. The ablation controlsystem according to claim 12, wherein the equation is of formv≈14.47[f₂(Δφ)×P×t_(e)], where v is the lesion volume, Δφ isrepresentative of the determined contact condition, P is representativeof the power level, t_(e) is representative of the measured time period,and f₂ is a frequency of the ablative energy.